JP2012511988A - X-ray inspection apparatus and method - Google Patents

X-ray inspection apparatus and method Download PDF

Info

Publication number
JP2012511988A
JP2012511988A JP2011541674A JP2011541674A JP2012511988A JP 2012511988 A JP2012511988 A JP 2012511988A JP 2011541674 A JP2011541674 A JP 2011541674A JP 2011541674 A JP2011541674 A JP 2011541674A JP 2012511988 A JP2012511988 A JP 2012511988A
Authority
JP
Japan
Prior art keywords
ray
rays
ray source
sources
source
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Granted
Application number
JP2011541674A
Other languages
Japanese (ja)
Other versions
JP5604443B2 (en
Inventor
フォグトマイヤー,ゲレオン
ボイマー,クリスティアン
Original Assignee
コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority to EP08171891.8 priority Critical
Priority to EP08171891 priority
Application filed by コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ filed Critical コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ
Priority to PCT/IB2009/055661 priority patent/WO2010070554A1/en
Publication of JP2012511988A publication Critical patent/JP2012511988A/en
Application granted granted Critical
Publication of JP5604443B2 publication Critical patent/JP5604443B2/en
Application status is Active legal-status Critical
Anticipated expiration legal-status Critical

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/40Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis
    • A61B6/405Source units adapted to modify characteristics of the beam during the data acquisition process
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/02Devices for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/03Computerised tomographs
    • A61B6/032Transmission computed tomography [CT]
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/40Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis
    • A61B6/4021Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis involving movement of the focal spot
    • A61B6/4028Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis involving movement of the focal spot resulting in acquisition of views from substantially different positions, e.g. EBCT
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/40Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis
    • A61B6/4035Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis the source being combined with a filter or grating
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/42Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4208Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector
    • A61B6/4241Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector using energy resolving detectors, e.g. photon counting
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/48Diagnostic techniques
    • A61B6/482Diagnostic techniques involving multiple energy imaging
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/40Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis
    • A61B6/4007Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis characterised by using a plurality of source units

Abstract

  The present invention relates to an inspection apparatus and corresponding method for realizing a spectral X-ray imaging apparatus by inverse geometry CT. The proposed inspection apparatus includes an X-ray source unit having a plurality of X-ray sources that emit X-rays at a plurality of positions, and X-rays emitted from one or more of the X-ray sources. An X-ray detection unit that generates a detection signal after detection through the inspection region between the X-ray detection unit and the X-ray detection unit, a processing unit that processes the generated detection signal, and sequentially in at least two different energy spectra Alternatively, a control unit that controls an X-ray source to emit X-rays in groups, during a time interval during which a particular X-ray source or group of X-ray sources is switched to emit X-rays with different energy spectra A particular X-ray source or group of X-ray sources is switched off and one or more other X-ray sources or groups of X-ray sources are sequentially switched on to emit X-rays. And a control unit for.

Description

  The present invention relates to an X-ray examination apparatus and a corresponding method, and a computer program for controlling the apparatus.

  Color (or spectral) X-ray imaging has been identified by all vendors of medical CT scanners as a very promising line for future development of CT (Computerized Tomography). However, CT vendors are of course following different approaches to get into the spectral domain. This is mainly due to the fact that the hardware implementation of a spectral CT scanner is not a simple task.

  For example, in the new 'inverse' geometry CT (IGCT) system design described in Non-Patent Document 1, a large distributed X-ray source with an array of individual electron emitters and focal points and a high frame rate A flat panel X-ray detector is used. With the advent of carbon nanotubes (CNT), as described in Non-Patent Document 2, for example, an X-ray generator capable of high-speed switching can be constructed as a cold 'electron gun'. Such CNT-based X-ray sources can be arranged in an array in the inverse geometry CT system described above and switched on and off in time according to a predetermined modulation pattern.

Known spectral CT systems must overcome the following technical obstacles or have the following disadvantages:
Dual source CT system with different kVp (peak kilovolt) settings: only two material components can be clearly separated; equipped with two sources (X-ray source) and two detectors The hardware cost is high,
Dual-layer detector: Only two material components can be clearly separated; the detector manufacturing process is complex,
Fast dual kVp switching: Only two material components can be clearly separated; strong kV transitions are difficult to achieve, so low spectral separation,
Photon counting spectrum CT: detection requires high hardware effort.

DeMan, B. et al., "Inverse geometry CT: The next-generation CT architecture?", IEEE Nuclear Science Symposium Conference Record, 2007, M07-2, pp.2715-2716 Liu, Z. et al., "Carbon nanotube based microfocus field emission x-ray source for microcomputed tomography", Applied Physics Letters, 2006, 89, 103111.

  One object of the present invention is an X-ray examination apparatus, in particular an X-ray examination apparatus having an inverse CT geometry, and a corresponding method, which can solve the above-mentioned obstacles and drawbacks, and the control of the apparatus. To provide a computer program.

In the first aspect of the present invention,
An X-ray source unit having a plurality of X-ray sources emitting X-rays at a plurality of positions;
-X-ray detection for detecting X-rays emitted from one or more of the X-ray sources after passing through an examination region between the X-ray source unit and the X-ray detection unit and generating a detection signal unit,
A processing unit for processing the generated detection signals, and a control unit for controlling the X-ray source so as to emit X-rays, individually or in groups, in at least two different energy spectra During a time interval in which the source or group of X-ray sources is switched to emit X-rays with different energy spectra, the particular X-ray source or group of X-ray sources is switched off and one or more A control unit for controlling other X-ray sources or groups of X-ray sources to emit X-rays in turn, individually or in groups,
An X-ray examination apparatus having

  In a further aspect of the invention, a corresponding method is presented.

  In yet a further aspect of the present invention, a computer having program code that, when executed on a computer, causes the computer to control the previously defined X-ray examination apparatus to perform the steps of the method described above. A program is presented.

  Preferred embodiments of the invention are defined in the dependent claims. As will be appreciated, the claimed method and the claimed computer program have the same and / or the same preferred embodiment as defined in the claimed device and in the dependent claims. Have.

  The present invention, particularly with respect to spectral CT applications, is based on the idea of using an inverse CT system configuration in which only one X-ray source or a group of X-ray sources (not all) are active at any given time. Based. Switching a particular x-ray source or group of x-ray sources to achieve emitting x-rays with a different energy spectrum than required, as required in spectral CT applications, takes some time . The time to switch this particular x-ray source or group of x-ray sources is in accordance with the invention so that in the meantime the particular x-ray source or group of x-ray sources is switched off and emits x-rays. One or more x-ray sources or groups of x-ray sources—sequentially and preferably only one or a group at a time—can be used to switch on. Therefore, even during this time, a detection signal is obtained and time is greatly saved. Thus, according to the present invention, the inverse CT source modulation pattern is extended by an advantageous alternating kV modulation scheme.

  A further advantage is a shortened acquisition time and thus smaller motion artifacts and better time resolution. If non-ideal effects are considered, switching can be described by transient behavior. For example, given the “slow” thermal emitter at the source and the “afterglow” at the detector, there is a smaller overlap of the different energy spectra if the signal from the previous frame leaks into the current acquisition frame.

  According to one embodiment, the control unit controls the X-ray source so that a specific X-ray source or group of X-ray sources is switched to emit X-rays with different energy spectra as soon as possible. Adapted to. Therefore, the other X-ray source is switched on only during the minimum period. As soon as the process of switching the first (specific) x-ray source or the first group of x-ray sources is completed, this x-ray source (or this group of x-ray sources) is switched on again and a new energy spectrum is obtained. X-rays are emitted. Preferably, this period is predetermined in order to properly control the timing of switching of the X-ray source. However, it is possible to determine this period and timing 'on-line' during the switching process itself.

  According to another embodiment, the control unit is arranged to turn on sequentially one or more other X-rays that are switched on during a time interval during which a particular X-ray source or group of X-ray sources is switched. A source or group of X-ray sources emits X-rays in the energy spectrum of the X-rays that the particular X-ray source or group of X-ray sources had previously emitted or would have emitted after being switched Adapted to control the X-ray source. Thus, all detection signals during a certain period (and from a certain projection angle range) are collected with the same energy spectrum of X-rays. This can be advantageous in data processing and reconstruction. It is also possible for part of the acquisition to be done in one fixed spectrum and the other part to be collected in dual energy mode or multi energy mode depending on the region of interest, which provides further flexibility.

  More preferably, the control unit is arranged such that the first group of X-ray sources emits X-rays individually, separately and sequentially in the at least two different energy spectra, after which the X-ray source Controlling the X-ray sources to emit X-rays in groups so that other groups of X-ray sources emit X-rays alone, separately and sequentially in the at least two different energy spectra. To be adapted. The advantages are different group sizes as an optimization for minimizing the number of spectrum switching operations, and the time resolution is sufficiently high.

  There are various options available for switching the x-ray source to emit x-rays in different energy spectra. Preferably, the control unit is adapted to switch the X-ray source to emit X-rays in different energy spectra, in particular by changing the voltage of the X-ray source, which is the voltage supplied to the anode of the X-ray source. The This allows for a simple X-ray source control and switching process.

  For this purpose, the device preferably further comprises a high voltage supply unit having a number of high voltage supply lines, the control unit dynamically connecting the X-ray source to the respective supply lines according to a switching pattern. Has a multiplexer.

  According to an advantageous embodiment, the X-ray source is a distributed X-ray, which is an X-ray source based on a field emitter, such as an X-ray source with a field emitter based on carbon nanotubes in particular (eg microfocus). Is the source. Such a distributed X-ray source saves space and can be easily controlled. Also, collection can be much faster when CNTs are used that can be arranged as an array on a planar substrate. Also, conventional thermal emitter technology may be used to construct a distributed X-ray source. Also, scattering artifacts are minimized. Furthermore, the distributed X-ray source makes it possible to inspect objects from different viewing angles without using mechanical movement. A set of projection images from different viewing angles allows limited 3D image reconstruction (eg, tomosynthesis). This tomographic scheme simplifies the construction and operation of the imaging device.

  Preferably, the apparatus further comprises a gantry on which the X-ray source unit and the X-ray detection unit are mounted and configured to rotate around the examination area. In particular, the gantry may be configured such that one or more of each of these units or each can rotate around the examination area. The advantage of using a distributed X-ray source is that such a device does not require mechanical movement / rotation. In other embodiments, a gantry is provided, particularly for movement / rotation of the x-ray source and / or detector. Even on such a gantry, a distributed X-ray source can be used.

  In a preferred embodiment, the X-ray detection unit comprises a multilayer detector, in particular a two-layer detector, in which each layer is adapted to detect X-rays of a predetermined energy spectrum. Since the detector in inverse geometry only covers a smaller X-ray sensitivity area, the hardware cost is reduced. Such a double-layer detector itself is described, for example, in WO 2007/039840.

  According to another embodiment, the X-ray detection unit comprises an energy discriminating photon counting detector. Even when using this embodiment, a reduction in hardware cost is achieved due to a smaller detector area compared to a conventional CT detector size. Such energy discriminating photon counting detectors are, for example, Iwanczyk, J, S. et al., `` Photon Counting Energy Dispersive Detector Arrays for X-ray Imaging '', IEEE Nuclear Science Symposium Conference Record, 2007, M09-4, pp. .2741-2748.

  Furthermore, according to one embodiment, the apparatus further comprises overflow detection means for detecting whether there is an overflow in any pixel of the X-ray detector during X-ray detection, the control unit is active Adapted to reduce the current supplied to the x-ray source.

  The control unit has an optimized switching scheme, for example adaptively taking into account the hardware, in particular the high voltage generator, the switching time (for example a source such as CNT), the region of interest and the required spatial resolution. It can also be adapted to determine.

  In one embodiment, the control unit is arranged such that a first group of X-ray sources emits X-rays having overlapping energy spectra, after which other groups of X-ray sources are separated and sequentially, in particular with the same energy. The X-ray source is adapted to be controlled to emit X-rays in groups so as to emit X-rays in the spectrum. This embodiment provides the advantage that an energy resolving detector can be used to identify the source, resulting in fast acquisition time and high accuracy.

The above and other aspects of the present invention will become apparent with reference to the embodiments described below.
It is a figure showing roughly one embodiment of the inspection device according to the present invention. FIG. 2 is a diagram illustrating an implementation example of the embodiment illustrated in FIG. 1 in a CT configuration. It is a three-dimensional perspective view showing a multi-source IGCT system. 1 is a diagram illustrating one embodiment of a field emission X-ray source based on carbon nanotubes. FIG. It is a figure which shows one Embodiment of an energy profile switching circuit. It is a figure which illustrates the switching system of the X-ray source according to this invention. It is a block diagram which shows one Embodiment of the control loop of the test | inspection apparatus according to this invention. It is a figure which illustrates the other switching system of the X-ray source according to this invention. In the drawings, identical or similar components are referred to by similar reference numerals.

  The technology according to the present application is generally directed to imaging technologies, such as tomosynthesis imaging technologies, that generate useful medical and non-medical images. As will be appreciated by those skilled in the art, the techniques of the present application can be applied to a variety of medical and non-medical applications, such as passenger and / or baggage screening, that provide useful three-dimensional data and context. In general, medical implementation examples are described to facilitate the description of the technology according to the present application, but as will be understood, non-medical implementations are also within the scope of the technology according to the present application.

  FIG. 1 schematically illustrates an exemplary embodiment of a multi-energy inspection apparatus 10 according to the present invention. The apparatus 10 includes a positioner or support 12 that supports an X-ray source unit 14. The support 12 may include one or more x-ray filters 16 that may be positioned between the x-ray source unit 14 and the desired imaging volume. In general, a digital detector 18 such as a flat panel detector is placed across the imaging volume from the X-ray source unit 14. The digital detector 18 may be stationary, or may move in cooperation with the X-ray source unit 14 and / or the support 12 or independently. A scattered radiation removal grid 20 may also exist between the digital detector 18 and the imaging volume. When present, the scattered radiation cancellation grid 20 is typically mounted near the digital detector 18 to suppress the incidence of scattered X-rays on the digital detector 18. In one embodiment, the scattered radiation cancellation grid may be steerable. In another embodiment, there is no scatter cancellation grid and instead algorithmic scatter correction can be performed to obtain a quantitative projection image.

  The X-ray source unit 14 emits X-rays from a plurality of positions within a limited angular range toward the whole or a part of the patient 22 located in an imaging volume including a region of interest in the patient 22. Configured as follows. The X-ray source unit 14 may be movable in various dimensions in one, two, or three dimensions, either manually or by automated means, so that the X-ray source unit 14 can be moved to the patient 22 and / or The position relative to the digital detector 18 can be changed.

  Preferably, in a CT configuration as shown in FIG. 2, the X-ray source unit 14 (having a number of dispersed X-ray sources 15) and the X-ray detector 18 rotate around the examination region 19 to gantry. 17 is attached. A support 21 such as a table supports a patient or other object in the examination area 19. The patient support 21 is preferably movable in the longitudinal or z direction. However, in a different embodiment, the X-ray source unit 14 and the X-ray detector 18 are not attached to the gantry and do not move.

  Typically, the x-ray source unit 14 is configured to emit x-rays in one or more spectra useful for imaging a desired object or patient 22. For example, in a medical situation, an X-ray source may emit an X-ray spectrum with high-energy photons, such as a 140 kVp spectrum with copper filtering, which can be used for patient imaging, or with desirable X-ray transmission characteristics. X-rays may be emitted in one or more low energy spectra (eg, unfiltered 90 kVp spectrum) each useful for patient imaging. X-rays can be generated by multiple generators (ie, X-ray tubes located at each of the desired radiation positions) placed or moved at a desired plurality of X-ray radiation positions, or within a desired angular range. The combination of the stationary X-ray tube 15 and the movable X-ray tube 15 arranged or movable at a plurality of desired radiation positions can be radiated from the X-ray source unit 14 at a number of positions.

  The aforementioned X-ray source 14 emits X-rays 24 (see FIG. 1) through the patient 22 toward the digital detector 18. Digital detector 18 typically includes a plurality of detector elements in an array configured to generate a digital signal in response to x-rays 24. In one embodiment of the invention, the digital detector 18 does not distinguish between the energy of the various photons that collide with the pixel. That is, each pixel represents the accumulated charge information of various X-ray spectra. In one such embodiment, the X-ray filter 16 is used to allow X-ray energy differentiation by limiting or changing the propagation spectrum at different points in time, for example to sequentially swap X-ray radiation. obtain. X-ray filter 16 may be made of copper, aluminum, iron, molybdenum, tin, barium, gadolinium, tungsten, lead, or other suitable material. Alternatively, in another embodiment of the present invention, the X-ray source 14 includes two X-ray sources 14 so that X-rays having an offset spectrum or energy profile can be propagated at different times without using the filter 16. It may be configurable to emit X-rays in the above spectrum.

  Alternatively, in yet another embodiment, the x-ray source unit 14 is not filtered or configured to emit in more than one spectrum (or only partially or specially filtered). ), The digital detector 18 may be an energy discriminating detector capable of distinguishing by itself X-rays 24 having different energy profiles or levels. For example, in one embodiment, the energy discrimination detector is used to capture both a high energy image and a low energy image for an X-ray source at a particular position in a single exposure. Similarly, in another embodiment, the digital detector 18 includes an array of scintillator and photodiode stacks configured to detect X-rays, each stack having a different spectral or energy profile. Also good. In this embodiment, the digital detector 18 can be used to capture a high energy image and a low energy image simultaneously.

  The operation of the X-ray source unit 14 can be controlled by the system controller 26. For example, the system controller 26 controls the activation and operation of the X-ray source unit 14 including collimation and timing via the X-ray controller 30. Also, in embodiments where the X-ray source unit 14 is configured to emit X-rays with more than one energy profile, the system controller 26 may specify the energy profile of the X-ray emission via an energy profile switching circuit 28. It may be configured to perform control or selection.

  The movement of the X-ray source unit 14 and / or the digital detector 18 may also be controlled by the system controller 26, for example by the motor controller 32, so as to move independently of each other or in synchronization. For example, in one embodiment, motor controller 32 may control the operation of positioner 12, such as a C-arm, to which X-ray source unit 14 and / or digital detector 18 are physically attached. In general, the positioner 12 realizes the physical operation of the X-ray source unit 14 and / or the digital detector 18 according to a predetermined imaging trajectory or an imaging trajectory selected by an operator. Thus, the positioner 12 allows the system controller 26 to facilitate the collection of x-ray projections at various angles through the patient. Alternatively, an embodiment in which the X-ray source unit 14 and the digital detector 18 are stationary, that is, a plurality of X-ray tubes or solid emitters fixed at different angles with respect to the detector 18 In the embodiment that 14 has, the positioner 12 is not present. Other hybrid configurations are possible as well, for example, in one embodiment, multiple x-ray sources moving as a set (ie, not individually) may be used. Further, in some embodiments, the patient or imaging object may be moved relative to the x-ray source and / or detector to create projection angles at various views over a finite angular range.

  The system controller 26 may also control the operation and readout of the digital detector 18, for example via the detector acquisition circuit 34. In one embodiment, the digital detector 18 converts the analog signal collected in response to x-rays into a digital signal and provides the digital signal to the detector acquisition circuit 34 for further processing. Typically, a processing circuit 36 is present to process and reconstruct the data read from the digital detector 18 by the detector acquisition circuit 34. Specifically, projection data or projection images are generated by the detector acquisition circuit 34 in response to X-rays emitted by the X-ray source unit 14. In embodiments where X-rays are generated or filtered to have different spectral or energy profiles at different times, the projection images are collected at a specific energy profile at all defined locations, and this process can be performed with other energy. Can be repeated for a profile. Alternatively, projection images may be collected for all energy profiles at a particular location and this process may be repeated for all defined locations. Other collection sequences are possible as well. However, in embodiments using an energy discriminating detector as the digital detector 18, typically only one projection image is acquired for each position since each projection image contains the desired energy information. Projection data collected by detector 18 may be pre-processed by detector collection circuit 34 and / or processing circuit 36. The processing circuit 36 may also reconstruct the projection data to generate one or more three-dimensional images for display.

  The processing circuit 36 may decompose the projection image based on the energy characteristics so as to associate the different energy characteristics with different material types. The processing circuit 36 may further reconstruct the projection image to generate a three-dimensional image such as a tomosynthesis image. These reconstruction and decomposition steps may be performed in any order, but in general, when both steps are performed, a composite 3D tomosynthesis image representing different material types or tissue types is generated. Can do. For example, the synthetic tomosynthesis image may include a soft tissue tomosynthesis image, a bone tomosynthesis image, and / or a contrast agent image. Conversely, if the processing circuitry reconstructs the collected projection data without decomposing the projection data, an energy tomosynthesis image, such as a low energy tomosynthesis image, an intermediate energy tomosynthesis image, and a high energy tomosynthesis image may be generated. These energy tomosynthesis images depict x-ray attenuation at the respective energy profile by the patient 22 or object within the imaging volume. In the medical context, various tomosynthesis images reveal the internal region of interest of the patient 22 and can be used for further diagnosis. The processing circuit 36 may also include a memory circuit that stores processed data and data to be processed. The memory circuit may also store processing parameters and / or computer programs.

  The processing circuit 36 may be connected to the operator workstation 40. The image generated by the processing circuit 36 may be sent to the operator workstation 40 for display on the display 42, for example. The processing circuitry 36 receives commands or processing parameters relating to processing, images or image data from an operator workstation 40 that may include input devices (not shown) such as a keyboard, mouse and other user interaction devices. Can be configured. The operator workstation 40 may also be connected to the system controller 26 to allow the operator to provide commands and scan parameters relating to the operation of the x-ray source unit 14 and / or detector 18 to the system controller 26. Thus, the operator can control the operation of the whole or part of the system 10 via the operator workstation 40.

  The operator workstation 40 is typically connected to a display 42 and / or a printer 44 that can render the image generated by the processing circuitry 36 (image display). Typically, display and / or printer circuitry within operator workstation 40 provides an image to a respective display 42 or printer 44 for rendering. The operator workstation 40 may also be connected to an image archiving communication system (PACS) 46. The PACS 46 can then be connected to the internal workstation 48 and / or the external workstation 50 via a network so that people at different locations can access the images and / or image data. Similarly, operator workstation 40 may access images or data accessible via PACS 46 for processing by processing circuitry 36 and / or rendering on display 42 or printer 44.

  FIG. 3 shows a multi-source using a small detector 18 combined with a large distributed source unit 14 in which a plurality of point x-ray sources 15 are arranged in the transverse direction (in the xy plane) and in the longitudinal direction (z-axis direction). A three-dimensional perspective view of an Inverse Geometry Computed Tomography (IGCT) system 10 is shown. Each of the point x-ray sources 15 emits a fan (fan) beam (or cone beam) 60 at different times, and projection data (eg, sinogram) 61 is captured by the detector 18. In addition, the detector 18, the distributed source unit 14, and the fan beam (or cone beam) 60 can be rotated about the rotation axis 62. The projection data 61 captured by the detector 18 is processed to reconstruct the object of interest in the field of view (inspection area) 19. Known re-binning algorithms can be used to re-bind projection data into parallel ray projections.

  In the transverse direction, the multiple point x-ray sources 15 are preferably rotated so that all corresponding fan beams (or cone beams) 60 are compatible with conventional third generation systems with isofocus detectors. Can be positioned on the isocentric arc. This allows for accurate reboiling into a complete cone beam and helps achieve a uniform beam profile. The resulting data set can be reorganized or re-boiled into a plurality of longitudinally offset third generation data sets. Also, the algorithm developed for multiple point x-ray sources 15 distributed in the z direction can be applied to multiple longitudinally offset axial scans using conventional third generation CT. The reverse is also true. For these reasons, it is desirable to position the sources on an isocentric arc, although other configurations such as arcs (arcs) centered on the detector and planar arrays may also be used.

  An X-ray tube is one possibility for X-ray generation by the X-ray source unit 14, and in other embodiments the X-ray source unit 14 may use other X-ray generation and emission techniques. For example, the X-ray source unit 14 may use a solid X-ray emitter instead of the X-ray tube in the above-described implementation. However, X-ray tubes and solid-state X-ray emitters are two examples of X-ray generation and emission techniques that can be used, others that can generate X-rays with a medically (or industrially) useful spectrum Any X-ray generation technique or apparatus may be used with the technique according to the present invention.

  In one embodiment, for example, an array of field emission X-ray sources 15 based on carbon nanotubes (CNT) is used for X-ray generation. As shown in FIG. 4, each source 15 of the array 14 includes a CNT cathode 151, a gate electrode 152, one or two focusing electrodes 153 and 154, and conversion of an electron beam 156 into an X-ray 157. Has an anode 155. Switching individual sources on and off is preferably accomplished by applying an appropriate voltage to the gate electrode 152.

  In accordance with the present invention, at a time interval in which a particular x-ray source is switched to emit x-rays of a different energy spectrum, the particular x-ray source is switched off and one or more other The system controller 26, specifically the energy profile switching circuit 28 and / or the X-ray controller 30, may be switched on and off separately and sequentially to emit at least two different energy spectra. Are adapted to control a plurality of X-ray sources 15 to emit X-rays separately and sequentially. Therefore, according to the present invention, an alternating kV modulation scheme is applied.

  A suitable implementation of the energy profile switching circuit 28 for individually controlling and switching a number of x-ray sources 15a, 15b,..., 15x is shown in FIG.

FIG. 6 illustrates an X-ray source switching method according to the present invention. For example, consider a particular source 15a that is switched on at time t 1 with a high voltage U 1 and switched off at time t 2 . The scan then proceeds to the other sources 15b, 15c of the X-ray generator. The time t 3, the source 15a is again activated at a high voltage U 2. during the time interval between t 2 and t 3, the high voltage source for the source 15a is switched from U 1 to U 2. Changing the high voltage takes some time that is usually given by the RC time constant of the high voltage supply wiring.

Thus, the described techniques alleviate the hardware effort associated with high voltage switching units by benefiting from fast switching of tubes (eg, CNTs) in the current domain. More specifically, the source 15a, 15b, the anode of 15c during the period from t 1 to t 2 can is coupled to the voltage U 1. At time t 2, the anode of the source 15a is already can be switched to a voltage U 2, being activated by using the gate voltage is not until the time t 3. When CNT is used as the source, the high voltage switching from U 1 to U 2 by using high voltage switching can be performed more slowly while achieving this activation at high speed. This separation of the high voltage switching of the anode voltage from the activation by the gate voltage achieves the advantages of using the switching sequence described above.

  Preferably, the inspection apparatus proposed according to the invention, in particular an inverse CT system, comprises a multi-layer detector. An advantage compared to multi-layer detectors and conventional CT geometries is that hardware costs are reduced. This is because the detector in the inverse geometry targets a smaller X-ray sensitivity region. Therefore, in one embodiment, a source switching pattern with two high voltage settings as shown in FIG. 6 and a dual layer detector form a “Quad-Energy CT” with an inverse geometry.

  In an alternative embodiment, the inspection device proposed according to the invention, in particular an inverse CT system, comprises an energy-discriminating counting mode detector. Again, the advantage is a reduction in hardware costs due to the smaller detector area. The counting mode detector is intended for a dynamic range with a limited X-ray intensity. To better address this feature, a control loop may be constructed that includes a detector pixel that adjusts the x-ray intensity and an x-ray source. Thus, the imaging system has a detector with real dose sensing capability along with an X-ray source having a virtual bow-tie filter. One implementation of the control loop performs x-ray source current reduction, for example, when it is indicated that at least one of the detector pixel groups is count rate saturated.

  In the preferred embodiment, there are a number of high voltage wirings 73, typically up to 150 kV, supplied by a high voltage generation unit 72a having one or more high voltage generators, as shown in FIG. . For example, there may be two high voltage generators for a fixed voltage, two energy supply, or three high voltage generators for a three energy supply. Alternatively, there are two high voltage generators, one of these generators providing the voltage to the active x-ray source and the other generator being the next required (higher, Alternatively, it may be switched to a lower voltage.

  This can be achieved by using the lowest high voltage setting as a reference and adding a certain amount of potential for the other setting. The anodes 155 of the individual sources 15a, 15b,..., 15x are dynamically connected to separate high voltage wirings 73. The corresponding focusing electrodes 153, 154 and gate electrode 152 of each source are connected to a further voltage source 72b and set at a constant rate of the anode potential. A time-controlled multiplexer 74 connects the set of anodes 155 (and focusing electrodes 153, 154 and gate electrodes 152 according to alternative embodiments) to the respective high voltage wiring 73 (with respect to the anode) according to the source switching pattern. , 75 (with respect to the focusing electrodes 153, 154 and the gate electrode 152). The multiplexer 74 is controlled by, for example, a microprocessor or FPGA 71 connected to a data acquisition system (34 in FIG. 1) for synchronization of the X-ray generator and detector.

  In one embodiment, a detector composed of pixels with a top layer of gadolinium oxysulfide (GOS) and a bottom layer of GOS with a photodiode readout at the end is used.

  According to another embodiment, a semiconductor sensor composed of pixels, for example made of Cd (Zn) Te, and associated counting electronics, for example with a shaping amplifier, a discriminator and a corresponding counter in each pixel; Is used. One embodiment of the control loop of the inspection apparatus of such an embodiment is shown in the block diagram of FIG. This control loop prevents count rate saturation in the detector pixels of detector 18. Within each electronic pixel 80, there is an overflow detection unit 81 that outputs an overflow flag (OF) 82. The overflow detection is executed within a predetermined time interval ('subframe') shorter than the frame time for reading by the counter 83. The period of the subframe is determined by the digital signal OF enable. After each subframe, the OFs of all pixels are combined by an OR circuit 84 that can be executed fairly quickly. If at least one pixel indicates an overflow, the current control unit 85 reduces the tube current and resets the saturated pixel counter 83. The loop with overflow detection and current reduction stops when no pixel points to overflow. The frame reading of the counter 83 also preferably captures the number of channel resets during the acquisition time frame. Thus, pixels that do not have overflow problems do not lose photon recording, and pixels that overflow in a subframe still have reasonable statistics. OF is the counter 83 entry, time over threshold information, or within a subframe measured using, for example, CIX type readout electronics (simultaneous counting and integration is facilitated by appropriate electronics based on signal replication) Can be obtained from the integral charge at.

  The geometry of the inspection device is selected according to the application. As described above, in one scenario, the source array and detector are mounted on the CT gantry and rotate around the object during data acquisition. In another scenario, the detector and source array remain stationary and the object is sampled with a smaller set of viewing angles.

  Image reconstruction is performed according to various techniques. One applicable technique is described, for example, in Dobbins J., “Digital x-ray tomosynthesis: current state of the art and clinical potential”, Phys. Med. Biol., 2003, Vol. 48, R65-R106. It is tomosynthesis. However, other techniques such as filtered back projection (Feldkamp) methods or iterative algorithms, which are well known in the art, may be applied as well. In this mode, the frame time can be dynamically adapted according to the final beam intensity set by the control loop.

  It is also possible that a single anode acts as a common anode for 2-3 emitters, or 2-3 anodes can be provided for a single emitter. For example, multiple anodes of different materials may be provided, for example, to emit different or overlapping energy spectra.

FIG. 8 illustrates another switching scheme of the X-ray source according to the present invention. According to this embodiment, the X-ray sources are switched on in groups, rather than switched on one at a time. For example, the source 15a, 15d, the first group of 15g is switched on at a high voltage U 1 to time t 1, it is switched off to the time t 2. The scan then proceeds to another group of sources 15b, 15e, 15h and then to the group of X-ray generator sources 15c, 15f, 15i. The time t 3, the source 15a of the first group, 15d, 15 g is again activated at a high voltage U 2. during the time interval between t 2 and t 3, the source 15a, 15d, a high voltage source for 15g group is switched from U 1 to U 2.

  Preferably, the X-ray sources assigned to a particular group have no or little overlap in the energy spectrum. An energy resolving detector is used that is tuned so that the recorded photons can be assigned to one of the active sources with a high probability. Thus, the resulting Poisson error is very low compared to conventional approaches where two (large) numbers with high quantum noise must be subtracted. The advantage is fast timing while reducing motion artifacts.

  The main applications of the present invention are computed tomography with energy resolution, projection imaging with energy resolution, or other applications that can benefit from energy-resolved X-ray photon counting.

  While the invention has been illustrated and described in detail in the drawings and foregoing description, such illustration and description are to be considered illustrative or exemplary and not restrictive. The invention is not limited to the disclosed embodiments. Other variations to the disclosed embodiments can be understood and realized by those skilled in the art upon reviewing the drawings, specification and claims, and practicing the claimed invention.

  In the claims, the term “comprising” does not exclude other elements or steps, and the indefinite article “a” or “an” does not exclude a plurality. A single element or other device may fulfill the functions of several items recited in the claims. The mere fact that certain measures are recited in mutually different dependent claims does not indicate that a combination of these measures cannot be used to advantage.

  The computer program may be stored / distributed on a suitable medium such as an optical storage medium or a solid medium provided with other hardware or parts thereof, but for example via the Internet or other wired or wireless telecommunication systems. It may be distributed in other forms.

  Any reference signs in the claims should not be construed as limiting the scope.

Claims (14)

  1. An X-ray source unit having a plurality of X-ray sources emitting X-rays at a plurality of positions;
    -X-ray detection for detecting X-rays emitted from one or more of the X-ray sources after passing through an examination region between the X-ray source unit and the X-ray detection unit and generating a detection signal unit,
    A processing unit for processing the generated detection signals, and a control unit for controlling the X-ray source so as to emit X-rays, individually or in groups, in at least two different energy spectra. During a time interval in which the source or group of X-ray sources is switched to emit X-rays with different energy spectra, the particular X-ray source or group of X-ray sources is switched off and one or more A control unit for controlling other X-ray sources or groups of X-ray sources to be switched on sequentially and emit X-rays;
    X-ray inspection apparatus.
  2.   The control unit is adapted to control the X-ray source so that the specific X-ray source or group of X-ray sources is switched to emit X-rays in the different energy spectrum as soon as possible. The X-ray inspection apparatus according to claim 1.
  3.   The control unit is configured to turn on one or more other X-ray sources or X-ray sources that are sequentially turned on during the time interval when the specific X-ray source or group of X-ray sources is switched. The X-rays so that the group of X-rays emits in the energy spectrum of the X-rays that the particular X-ray source or group of X-ray sources had previously emitted or switched off The x-ray examination apparatus of claim 1, wherein the x-ray examination apparatus is adapted to control the source.
  4.   The control unit is configured such that a first group of X-ray sources emits X-rays alone, separately and sequentially in the at least two different energy spectra, after which other X-ray sources Controlling the X-ray sources to emit X-rays in groups such that a group of X-ray sources emit X-rays alone, separately and sequentially in the at least two different energy spectra; The X-ray examination apparatus according to claim 1, which is adapted.
  5.   The control unit is specifically adapted to switch the X-ray source to emit X-rays in different energy spectra by changing the voltage of the X-ray source, which is the voltage supplied to the anode of the X-ray source. The X-ray inspection apparatus according to claim 1.
  6.   6. The high voltage supply unit further comprising a plurality of high voltage supply lines, wherein the control unit includes a multiplexer that dynamically connects the X-ray source to each of the supply lines according to a switching pattern. The X-ray inspection apparatus described.
  7.   The x-ray source according to claim 1, wherein the x-ray source is a distributed x-ray source, in particular an x-ray source based on a field emitter such as a microfocus x-ray source with a field emitter based on carbon nanotubes. Inspection device.
  8.   The X-ray inspection apparatus according to claim 1, further comprising a gantry on which the X-ray source unit and the X-ray detection unit are mounted and configured to rotate around the inspection region.
  9.   The X-ray inspection apparatus according to claim 1, wherein the X-ray detection unit comprises a multi-layer detector, in particular a double-layer detector, each layer adapted to detect X-rays of a predetermined energy spectrum.
  10.   The X-ray inspection apparatus according to claim 1, wherein the X-ray detection unit includes an energy discrimination photon counting detector.
  11.   The apparatus further comprises overflow detection means for detecting whether an overflow exists in any pixel of the X-ray detector during X-ray detection, and the control unit reduces a current supplied to an active X-ray source. The X-ray examination apparatus according to claim 10, which is adapted as follows.
  12.   The control unit emits X-rays with a first group of X-ray sources having overlapping energy spectra, after which a plurality of other groups of X-ray sources are separated and sequentially, in particular with the same energy spectrum. The X-ray examination apparatus according to claim 1, wherein the X-ray source is adapted to control the X-ray source to emit X-rays in groups.
  13. -Emitting X-rays at a plurality of positions by an X-ray source unit having a plurality of X-ray sources;
    -Detecting X-rays emitted from one or more of the X-ray sources after penetrating an examination region between the X-ray source unit and the X-ray detection unit, and generating a detection signal;
    Processing the generated detection signal, and controlling the X-ray source to emit X-rays in sequence, alone or in groups, in at least two different energy spectra, the specific X-ray source Or during a time interval in which the group of X-ray sources is switched to emit X-rays in different energy spectra, the particular X-ray source or group of X-ray sources is switched off and one or more other Controlling the X-ray source or group of X-ray sources to be switched on separately and sequentially to emit X-rays;
    X-ray inspection method comprising:
  14.   A computer program comprising program code that, when executed on a computer, causes the computer to control the X-ray examination apparatus according to claim 1 to perform the steps of the method according to claim 13.
JP2011541674A 2008-12-17 2009-12-10 X-ray inspection apparatus and method Active JP5604443B2 (en)

Priority Applications (3)

Application Number Priority Date Filing Date Title
EP08171891.8 2008-12-17
EP08171891 2008-12-17
PCT/IB2009/055661 WO2010070554A1 (en) 2008-12-17 2009-12-10 X-ray examination apparatus and method

Publications (2)

Publication Number Publication Date
JP2012511988A true JP2012511988A (en) 2012-05-31
JP5604443B2 JP5604443B2 (en) 2014-10-08

Family

ID=41808991

Family Applications (1)

Application Number Title Priority Date Filing Date
JP2011541674A Active JP5604443B2 (en) 2008-12-17 2009-12-10 X-ray inspection apparatus and method

Country Status (6)

Country Link
US (1) US8699657B2 (en)
EP (1) EP2378974B1 (en)
JP (1) JP5604443B2 (en)
CN (1) CN102256548B (en)
RU (1) RU2523827C2 (en)
WO (1) WO2010070554A1 (en)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
KR20160050686A (en) * 2014-10-30 2016-05-11 서강대학교산학협력단 Signal processing system and method for medical image equipment using multi threshold voltage

Families Citing this family (29)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102009058266B4 (en) 2009-12-14 2020-01-02 Siemens Healthcare Gmbh Medical X-ray system
US10165992B2 (en) * 2010-10-18 2019-01-01 Carestream Health, Inc. X-ray imaging systems and devices
CN103181772A (en) * 2011-10-09 2013-07-03 明峰医疗系统股份有限公司 Multi-source low dose x-ray ct imaging aparatus
DE102010042683B4 (en) * 2010-10-20 2013-11-14 Siemens Aktiengesellschaft Device and method for generating X-radiation and computer program and data carrier
DE102010061882A1 (en) * 2010-11-24 2012-05-24 Siemens Aktiengesellschaft X-ray system and method for generating X-ray image data
US8532744B2 (en) 2011-08-23 2013-09-10 General Electric Company Method and system for design of spectral filter to classify tissue and material from multi-energy images
US9069092B2 (en) * 2012-02-22 2015-06-30 L-3 Communication Security and Detection Systems Corp. X-ray imager with sparse detector array
CN103308535B (en) * 2012-03-09 2016-04-13 同方威视技术股份有限公司 For equipment and the method for ray scanning imaging
US9237874B2 (en) 2012-04-30 2016-01-19 General Electric Company Method and system for non-invasive imaging of a target region
DE102012222714A1 (en) 2012-12-11 2014-06-12 Siemens Aktiengesellschaft Determination of a multiple energy image
CN103040481B (en) * 2012-12-25 2015-08-26 深圳先进技术研究院 A kind of system and method reducing x-ray diagnostic equipment x-ray dose
EP2987454A4 (en) * 2013-04-16 2016-09-21 Toshiba Medical Sys Corp X-ray ct device
JP6188470B2 (en) * 2013-07-24 2017-08-30 キヤノン株式会社 Radiation generator and radiation imaging system using the same
EP3066983A4 (en) * 2013-11-06 2017-08-30 Rayence Co., Ltd. X-ray imaging device including plurality of x-ray sources
CN105723243B (en) * 2013-11-15 2019-07-09 皇家飞利浦有限公司 Two-sided organic photodetector in flexible substrates
WO2015081035A1 (en) * 2013-11-26 2015-06-04 The Johns Hopkins University Dual-energy cone-beam computed tomography with a multiple source, single-detector configuration
US10048391B2 (en) * 2013-12-04 2018-08-14 Koninklijke Philips N.V. Imaging detector self-diagnosis circuitry
CN104749648A (en) * 2013-12-27 2015-07-01 清华大学 Multi-energy spectrum static CT apparatus
US9976971B2 (en) * 2014-03-06 2018-05-22 United Technologies Corporation Systems and methods for X-ray diffraction
CN103876772B (en) * 2014-03-20 2015-12-09 中北大学 A kind of multispectral formation method and device
US9277897B1 (en) * 2014-08-20 2016-03-08 ADANI Systems, Inc. Multi-beam stereoscopic X-ray body scanner
JP6441015B2 (en) * 2014-10-06 2018-12-19 キヤノンメディカルシステムズ株式会社 X-ray diagnostic apparatus and X-ray tube control method
GB2531326A (en) * 2014-10-16 2016-04-20 Adaptix Ltd An X-Ray emitter panel and a method of designing such an X-Ray emitter panel
DE102015213285A1 (en) 2015-07-15 2017-02-02 Siemens Healthcare Gmbh X-ray device for inverse computed tomography
US9888894B2 (en) * 2015-12-21 2018-02-13 General Electric Company Multi-energy X-ray imaging
US10571579B2 (en) * 2016-01-22 2020-02-25 General Electric Company Dual-mode radiation detector
WO2017185028A1 (en) * 2016-04-22 2017-10-26 Hologic, Inc. Tomosynthesis with shifting focal spot x-ray system using an addressable array
US9770221B1 (en) * 2016-07-01 2017-09-26 Siemens Medical Solutions Usa, Inc. Imaging using multiple energy levels
US20180038807A1 (en) * 2016-08-08 2018-02-08 Adaptix Ltd. Method and system for reconstructing 3-dimensional images from spatially and temporally overlapping x-rays

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2005288152A (en) * 2004-03-31 2005-10-20 General Electric Co <Ge> Rotational computed tomography system and method
WO2006123581A1 (en) * 2005-05-18 2006-11-23 Hitachi Medical Corporation Radiograph and image processing program
JP2006320464A (en) * 2005-05-18 2006-11-30 Hitachi Medical Corp Radiographic equipment and method for processing image
JP2007267980A (en) * 2006-03-31 2007-10-18 National Univ Corp Shizuoka Univ Continuous processing type x-ray ct apparatus without rotating mechanism

Family Cites Families (17)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5949848A (en) * 1996-07-19 1999-09-07 Varian Assocaites, Inc. X-ray imaging apparatus and method using a flat amorphous silicon imaging panel
US6876724B2 (en) * 2000-10-06 2005-04-05 The University Of North Carolina - Chapel Hill Large-area individually addressable multi-beam x-ray system and method of forming same
US7103137B2 (en) * 2002-07-24 2006-09-05 Varian Medical Systems Technology, Inc. Radiation scanning of objects for contraband
US7110500B2 (en) 2003-09-12 2006-09-19 Leek Paul H Multiple energy x-ray source and inspection apparatus employing same
US20050226364A1 (en) 2003-11-26 2005-10-13 General Electric Company Rotational computed tomography system and method
US7333587B2 (en) * 2004-02-27 2008-02-19 General Electric Company Method and system for imaging using multiple offset X-ray emission points
DE102004051820A1 (en) * 2004-10-25 2006-05-04 Siemens Ag Tomography apparatus and method for a tomography apparatus for generating multiple energy images
US7062006B1 (en) 2005-01-19 2006-06-13 The Board Of Trustees Of The Leland Stanford Junior University Computed tomography with increased field of view
CN101166469B (en) * 2005-04-26 2015-05-06 皇家飞利浦电子股份有限公司 Double decker detector for spectral CT
CN101313214B (en) * 2005-09-23 2013-03-06 北卡罗来纳大学查珀尔希尔分校 Methods, and systems for multiplexing computed tomography
WO2007088497A1 (en) * 2006-02-02 2007-08-09 Philips Intellectual Property & Standards Gmbh Imaging apparatus using distributed x-ray sources and method thereof
EP2029022B1 (en) * 2006-05-26 2012-12-05 Koninklijke Philips Electronics N.V. Multi-tube imaging system reconstruction
US7778386B2 (en) 2006-08-28 2010-08-17 General Electric Company Methods for analytic reconstruction for mult-source inverse geometry CT
US7813478B2 (en) 2007-02-08 2010-10-12 Varian Medical Systems, Inc. Method and apparatus to facilitate provision and use of multiple X-ray sources
US7869566B2 (en) * 2007-06-29 2011-01-11 Morpho Detection, Inc. Integrated multi-sensor systems for and methods of explosives detection
WO2009011422A1 (en) * 2007-07-19 2009-01-22 Hitachi Medical Corporation X-ray generator and x-ray ct scanner using the same
JP5582514B2 (en) * 2008-02-29 2014-09-03 ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー X-ray CT system

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2005288152A (en) * 2004-03-31 2005-10-20 General Electric Co <Ge> Rotational computed tomography system and method
WO2006123581A1 (en) * 2005-05-18 2006-11-23 Hitachi Medical Corporation Radiograph and image processing program
JP2006320464A (en) * 2005-05-18 2006-11-30 Hitachi Medical Corp Radiographic equipment and method for processing image
JP2007267980A (en) * 2006-03-31 2007-10-18 National Univ Corp Shizuoka Univ Continuous processing type x-ray ct apparatus without rotating mechanism

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
KR20160050686A (en) * 2014-10-30 2016-05-11 서강대학교산학협력단 Signal processing system and method for medical image equipment using multi threshold voltage
KR101646651B1 (en) 2014-10-30 2016-08-08 서강대학교산학협력단 Signal processing system and method for medical image equipment using multi threshold voltage

Also Published As

Publication number Publication date
RU2523827C2 (en) 2014-07-27
EP2378974B1 (en) 2013-04-03
EP2378974A1 (en) 2011-10-26
WO2010070554A1 (en) 2010-06-24
CN102256548A (en) 2011-11-23
CN102256548B (en) 2014-03-05
JP5604443B2 (en) 2014-10-08
RU2011129670A (en) 2013-01-27
US8699657B2 (en) 2014-04-15
US20110280367A1 (en) 2011-11-17

Similar Documents

Publication Publication Date Title
US9259194B2 (en) Method and apparatus for advanced X-ray imaging
Pauwels et al. Technical aspects of dental CBCT: state of the art
US10231687B2 (en) Method and apparatus for enhanced X-ray computing arrays
RU2594606C2 (en) Photon counting detector
EP2583250B1 (en) Method and system for performing low-dose ct imaging
DE10317612B4 (en) X-ray source with a curved surface cathode, imaging system and imaging method
US7082182B2 (en) Computed tomography system for imaging of human and small animal
US7039153B2 (en) Imaging tomography device with at least two beam detector systems, and method to operate such a tomography device
CN101296658B (en) X-ray imaging system using temporal digital signal processing
JP6014323B2 (en) X-ray system
JP2014061286A (en) X-ray ct device, image processing device, and image processing method
US9107642B2 (en) Method and apparatus for tomographic X-ray imaging and source configuration
JP4726995B2 (en) Fast kVp switching system and method for dual energy CT
US7065179B2 (en) Multiple target anode assembly and system of operation
US6399951B1 (en) Simultaneous CT and SPECT tomography using CZT detectors
JP4904349B2 (en) Detector and system for acquiring radiation data
JP5346654B2 (en) Radiation imaging apparatus and control method thereof
JP4759255B2 (en) Static computed tomography system and method
JP4599073B2 (en) X-ray tomography equipment
US9207332B2 (en) Counting digital x-ray image detector with two switchable modes
EP0948930B1 (en) Acquiring volumetric image data
US7751528B2 (en) Stationary x-ray digital breast tomosynthesis systems and related methods
JP5268499B2 (en) Computerized tomography (CT) imaging system
US7192031B2 (en) Emitter array configurations for a stationary CT system
JP4974131B2 (en) Imaging method and system using a plurality of offset X-ray irradiation points

Legal Events

Date Code Title Description
A621 Written request for application examination

Free format text: JAPANESE INTERMEDIATE CODE: A621

Effective date: 20121207

A977 Report on retrieval

Free format text: JAPANESE INTERMEDIATE CODE: A971007

Effective date: 20131015

A131 Notification of reasons for refusal

Free format text: JAPANESE INTERMEDIATE CODE: A131

Effective date: 20131022

A521 Written amendment

Free format text: JAPANESE INTERMEDIATE CODE: A523

Effective date: 20140121

TRDD Decision of grant or rejection written
A01 Written decision to grant a patent or to grant a registration (utility model)

Free format text: JAPANESE INTERMEDIATE CODE: A01

Effective date: 20140729

A61 First payment of annual fees (during grant procedure)

Free format text: JAPANESE INTERMEDIATE CODE: A61

Effective date: 20140825

R150 Certificate of patent or registration of utility model

Ref document number: 5604443

Country of ref document: JP

Free format text: JAPANESE INTERMEDIATE CODE: R150

R250 Receipt of annual fees

Free format text: JAPANESE INTERMEDIATE CODE: R250

R250 Receipt of annual fees

Free format text: JAPANESE INTERMEDIATE CODE: R250

R250 Receipt of annual fees

Free format text: JAPANESE INTERMEDIATE CODE: R250